Method and apparatus for automated image analysis of biological specimens

ABSTRACT

An electronic microscope system including a processor, a movable stage movable in two orthogonal directions under control of the processor, the movable stage including at least one part that determines a current position of the movable stage, a microscope part, which magnifies a sample on the movable stage, an electronic camera part, which obtains an image of a magnified sample at a specified position controlled by the movable stage, and at least one vibration isolation mount, coupled to the stage and isolating vibration between the movable stage and the microscope part.

RELATED APPLICATIONS

This application is a divisional of U.S. patent application Ser. No.11/594,374, filed Nov. 7, 2006, which is a continuation of U.S. patentapplication Ser. No. 11/115,847, filed Apr. 26, 2005, now U.S. Pat. No.7,133,545, which is a continuation of U.S. patent application Ser. No.10/404,921, filed Mar. 31, 2003, now U.S. Pat. No. 6,920,239, which is acontinuation of U.S. patent application Ser. No. 09/492,101, filed Feb.14, 2000, now U.S. Pat. No. 6,553,135, which is a continuation of U.S.patent application Ser. No. 08/758,436, filed Nov. 27, 1996, now U.S.Pat. No. 6,215,892, which claims the benefit of U.S. ProvisionalApplication No. 60/026,805, filed Nov. 30, 1995, each of which is herebyfully incorporated herein by reference.

BACKGROUND

In the field of medical diagnostics including oncology, the detection,identification, quantitation and characterization of cells of interest,such as cancer cells, through testing of biological specimens is animportant aspect of diagnosis. Typically, a biological specimen such asbone marrow, lymph nodes, peripheral blood, cerebrospinal fluid, urine,effusions, fine needle aspirates, peripheral blood scrapings or othermaterials are prepared by staining the specimen to identify cells ofinterest. One method of cell specimen preparation is to react a specimenwith a specific probe which can be a monoclonal antibody, a polyclonalantiserum, or a nucleic acid which is reactive with a component of thecells of interest, such as tumor cells. The reaction may be detectedusing an enzymatic reaction, such as alkaline phosphatase or glucoseoxidase or peroxidase to convert a soluble colorless substrate to acolored insoluble precipitate, or by directly conjugating a dye to theprobe.

Examination of biological specimens in the past has been performedmanually by either a lab technician or a pathologist. In the manualmethod, a slide prepared with a biological specimen is viewed at a lowmagnification under a microscope to visually locate candidate cells ofinterest. Those areas of the slide where cells of interest are locatedare then viewed at a higher magnification to confirm those objects ascells of interest, such as tumor or cancer cells. The manual method istime consuming and prone to error including missing areas of the slide.

Automated cell analysis systems have been developed to improve the speedand accuracy of the testing process. One known interactive systemincludes a single high power microscope objective for scanning a rack ofslides, portions of which have been previously identified for assay byan operator. In that system, the operator first scans each slide at alow magnification similar to the manual method and notes the points ofinterest on the slide for later analysis. The operator then stores theaddress of the noted location and the associated function in a datafile. Once the points of interest have been located and stored by theoperator, the slide is then positioned in an automated analysisapparatus which acquires images of the slide at the marked points andperforms an image analysis.

BRIEF SUMMARY

In an aspect, an electronic microscope system includes a processor, amovable stage movable in two orthogonal directions under control of theprocessor, the movable stage including at least one part that determinesa current position of the movable stage, a microscope part, whichmagnifies a sample on the movable stage, an electronic camera part,which obtains an image of a magnified sample at a specified positioncontrolled by the movable stage, and at least one vibration isolationmount, coupled to the stage and isolating vibration between the movablestage and the microscope part.

In another aspect, a method includes using a processor to move a sampleholding stage, magnifying an image of an area of the sample on themovable stage, wherein the area is based on a moved position of thesample holding stage, obtaining an electronic file indicative of themagnified image, and isolating vibration between the moving of the stageand the magnifying and obtaining.

In a further aspect, a method includes obtaining an electronic versionof a microscope image and determining information about colors withinthe image by establishing a high threshold and a low threshold for aspecified color, counting a number of pixels that are in between thehigh threshold and the low threshold, dividing the number of pixels by avalue which relates pixels to cell size, and using a resultant number asa count of the number of cells within the image.

In yet another aspect, a method includes staining a biological samplewith a stain of a specified color, obtaining an electronic version of amicroscope image of the biological sample, using the specified color todetermine high threshold and a low threshold around the specified color,analyzing the image, to determine information about areas in the imagethat are in between the high threshold and the low threshold, and usingthe information to determine a count of the number of stained cells inthe image.

BRIEF DESCRIPTION OF THE DRAWINGS

The above and other features of the invention including various noveldetails of construction and combinations of parts will now be moreparticularly described with reference to the accompanying drawings andpointed out in the claims. It will be understood that the particularapparatus embodying the invention is shown by way of illustration onlyand not as a limitation of the invention. The principles and features ofthis invention may be employed in varied and numerous embodimentswithout departing from the scope of the invention.

FIG. 1 is a perspective view of an apparatus for automated cell analysisembodying the present invention.

FIG. 2 is a block diagram of the apparatus shown in FIG. 1.

FIG. 3 is a block diagram of the microscope controller of FIG. 2.

FIG. 4 is a plan view of the apparatus of FIG. 1 having the housingremoved.

FIG. 5 is a side view of a microscope subsystem of the apparatus of FIG.1.

FIG. 6 a is a top view of a slide carrier for use with the apparatus ofFIG. 1.

FIG. 6 b is a bottom view of the slide carrier of FIG. 6 a.

FIG. 7 a is a top view of an automated slide handling subsystem of theapparatus of FIG. 1.

FIG. 7 b is a partial cross-sectional view of the automated slidehandling subsystem of FIG. 7 a taken on line A-A.

FIG. 8 is an end view of the input module of the automated slidehandling subsystem.

FIGS. 8 a-8 d illustrate the input operation of the automatic slidehandling subsystem.

FIGS. 9 a-9 d illustrate the output operation of the automated slidehandling subsystem.

FIG. 10 is a flow diagram of the procedure for automatically determininga scan area.

FIG. 11 shows the scan path on a prepared slide in the procedure of FIG.10.

FIG. 12 illustrates an image of a field acquired in the procedure ofFIG. 10.

FIG. 13A is a flow diagram of a preferred procedure for determining afocal position.

FIG. 133B is a flow diagram of a preferred procedure for determining afocal position for neutrophils stained with Fast Red and counterstainedwith hemotoxylin.

FIG. 14 is a flow diagram of a procedure for automatically determininginitial focus.

FIG. 15 shows an array of slide positions for use in the procedure ofFIG. 14.

FIG. 16 is a flow diagram of a procedure for automatic focusing at ahigh magnification.

FIG. 17A is a flow diagram of an overview of the preferred process tolocate and identify objects of interest in a stained biological specimenon a slide.

FIG. 17B is a flow diagram of a procedure for color space conversion.

FIG. 18 is a flow diagram of a procedure for background suppression viadynamic thresholding.

FIG. 19 is a flow diagram of a procedure for morphological processing.

FIG. 20 is a flow diagram of a procedure for blob analysis.

FIG. 21 is a flow diagram of a procedure for image processing at a highmagnification.

FIG. 22 illustrates a mosaic of cell images produced by the apparatus.

FIG. 23 is a flow diagram of a procedure for estimating the number ofnucleated cells in a scan area.

FIG. 24 illustrates the apparatus functions available in a userinterface of the apparatus.

DETAILED DESCRIPTION OF THE DRAWINGS

Referring now to the figures, an apparatus for automated cell analysisof biological specimens is generally indicated by reference numeral 10as shown in perspective view in FIG. 1 and in block diagram form in FIG.2. The apparatus 10 comprises a microscope subsystem 32 housed in ahousing 12. The housing 12 includes a slide carrier input hopper 16 anda slide carrier output hopper 18. A door 14 in the housing 12 securesthe microscope subsystem from the external environment. A computersubsystem comprises a computer 22 having a system processor 23, an imageprocessor 25 and a communications modem 29. The computer subsystemfurther includes a computer monitor 26 and an image monitor 27 and otherexternal peripherals including storage device 21, track ball device 30,keyboard 28 and color printer 35. An external power supply 24 is alsoshown for powering the system. Viewing oculars 20 of the microscopesubsystem project from the housing 12 for operator viewing. Theapparatus 10 further includes a CCD camera 42 for acquiring imagesthrough the microscope subsystem 32. A microscope controller 31 underthe control of system processor 23 controls a number ofmicroscope-subsystem functions described further in detail. An automaticslide feed mechanism 37 in conjunction with X-Y stage 38 provideautomatic slide handling in the apparatus 10. An illumination lightsource 48 projects light onto the X-Y stage 38 which is subsequentlyimaged through the microscope subsystem 32 and acquired through CCDcamera 42 for processing in the image processor 25. A Z stage or focusstage 46 under control of the microscope controller 31 providesdisplacement of the microscope subsystem in the Z plane for focusing.The microscope subsystem 32 further includes a motorized objectiveturret 44 for selection of objectives.

The purpose of the apparatus 10 is for the unattended automatic scanningof prepared microscope slides for the detection and counting ofcandidate objects of interest such as normal and abnormal cells, e.g.,tumor cells. The preferred embodiment may be utilized for rare eventdetection in which there may be only one candidate object of interestper several hundred thousand normal cells, e.g., one to five candidateobjects of interest per 2 square centimeter area of the slide. Theapparatus 10 automatically locates and counts candidate objects ofinterest and estimates normal cells present in a biological specimen onthe basis of color, size and shape characteristics. A number of stainsare used to preferentially stain candidate objects of interest andnormal cells different colors so that such cells can be distinguishedfrom each other.

As noted in the background of the invention, a biological specimen maybe prepared with a reagent to obtain a colored insoluble precipitate.The apparatus of the present invention is used to detect thisprecipitate as a candidate object of interest.

During operation of the apparatus 10, a pathologist or laboratorytechnician mounts prepared slides onto slide carriers. A slide carrier60 is illustrated in FIG. 8 and will be described further below. Eachslide carrier holds up to 4 slides. Up to 25 slide carriers are thenloaded—into input hopper 16. The operator can specify the size, shapeand location of the area to be scanned or alternatively, the system canautomatically locate this area. The operator then commands the system tobegin automated scanning of the slides through a graphical userinterface. Unattended scanning begins with the automatic loading of thefirst carrier and slide onto the precision motorized X-Y stage 38. A barcode label affixed to the slide is read by a bar code reader 33 duringthis loading operation. Each slide is then scanned at a user selectedlow microscope magnification, for example, 10×, to identify candidatecells based on their color, size and shape characteristics. The X-Ylocations of candidate cells are stored until scanning is completed.

After the low magnification scanning is completed, the apparatusautomatically returns to each candidate cell, reimages and refocuses ata higher magnification such as 40× and performs further analysis toconfirm the cell candidate. The apparatus stores an image of the cellfor later review by a pathologist. All results and images can be storedto a storage device 21 such as a removable hard drive or DAT tape ortransmitted to a remote site for review or storage. The stored imagesfor each slide can be viewed in a mosaic of images for further review.In addition, the pathologist or operator can also directly view adetected cell through the microscope using the included oculars 20 or onimage monitor 27.

Having described the overall operation of the apparatus 10 from a highlevel, the further details of the apparatus will now be described.Referring to FIG. 3, the microscope controller 31 is shown in moredetail. The microscope controller 31 includes a number of subsystemsconnected through a system bus. A system processor 102 controls thesesubsystems and is controlled by the apparatus system processor 23through an RS 232 controller 110. The system processor 102 controls aset of motor-control subsystems 114 through 124 which control the inputand output feeder, the motorized turret 44, the X-Y stage 38, and the Zstage 46 (FIG. 2). A histogram processor 108 receives input from CCDcamera 42 for computing variance data during the focusing operationdescribed further herein.

The system processor 102 further controls an illumination controller 106for control of substage illumination 48. The light output from thehalogen light bulb which supplies illumination for the system can varyover time due to bulb aging, changes in optical alignment, and otherfactors. In addition, slides which have been “over stained” can reducethe camera exposure to an unacceptable level. In order to compensate forthese effects, the illumination controller 106 is included. Thiscontroller is used in conjunction with light control software tocompensate for the variations in light level. The light control softwaresamples the output from the camera at intervals (such as between loadingof slide carriers), and commands the controller to adjust the lightlevel to the desired levels. In this way, light control is automatic andtransparent to the user and adds no additional time to system operation.

The system processor 23 is preferably comprised of dual parallel IntelPentium 90 MHz devices. The image processor 25 is preferably a MatroxImaging Series 640 model. The microscope controller system processor 102is an Advanced Micro Devices AMD29K device.

Referring now to FIGS. 4 and 5, further detail of the apparatus 10 isshown. FIG. 4 shows a plan view of the apparatus 10 with the housing 12removed. A portion of the automatic slide feed mechanism 37 is shown tothe left of the microscope subsystem 32 and includes slide carrierunloading assembly 34 and unloading platform 36 which in conjunctionwith slide carrier output hopper 18 function to receive slide carrierswhich have been analyzed.

Vibration isolation mounts 40, shown in further detail in FIG. 5, areprovided to isolate the microscope subsystem 32 from mechanical shockand vibration that can occur in a typical laboratory environment. Inaddition to external sources of vibration, the high speed operation ofthe X-Y stage 38 can induce vibration into the microscope subsystem 32.Such sources of vibration can be isolated from the electro-opticalsubsystems to avoid any undesirable effects on image quality. Theisolation mounts 40 comprise a spring 40 a and piston 40 b submerged ina high viscosity silicon gel which is enclosed in an elastomer membranebonded to a casing to achieve damping factors on the order of 17 to 20%.

The automatic slide handling feature of the present invention will nowbe described. The automated slide handling subsystem operates on asingle slide carrier at a time. A slide carrier 60 is shown in FIGS. 6 aand 6 b which provide a top view and a bottom view respectively. Theslide carrier 60 includes up to four slides 70 mounted with adhesivetape 62. The carrier 60 includes ears 64 for hanging the carrier in theoutput hopper 18. An undercut 66 and pitch rack 68 are formed at the topedge of the slide carrier 60 for mechanical handling of the slidecarrier. A keyway cutout 65 is formed in one side of the carrier 60 tofacilitate carrier alignment. A prepared slide 72 mounted on the slidecarrier 60 includes a sample area 72 a and a bar code label area 72 b.

FIG. 7 a provides a top view of the slide handling subsystem whichcomprises a slide input module 15, a slide output module 17 and X-Ystage drive belt 50. FIG. 7 b provides a partial cross-sectional viewtaken along line A-A of FIG. 7 a.

The slide input module 15 comprises a slide carrier input hopper 16,loading platform 52 and slide carrier loading subassembly 54. The inputhopper 16 receives a series of slide carriers 60 (FIGS. 6 a and 6 b) ina stack on loading platform 52. A guide key 57 protrudes from a side ofthe input hopper 16 to which the keyway cutout 65 (FIG. 6 a) of thecarrier is fit to achieve proper alignment.

The input module 15 further includes a revolving indexing cam 56 and aswitch 90 mounted in the loading platform 52, the operation of which isdescribed further below. The carrier loading subassembly 54 comprises aninfeed drive belt 59 driven by a motor 86. The infeed drive belt 59includes a pusher tab 58 for pushing the slide carrier horizontallytoward the X-Y stage 38 when the belt is driven. A homing switch 95senses the pusher tab 58 during a revolution of the belt 59.

Referring specifically to FIG. 7 a, the X-Y stage 38 is shown with xposition and y position motors 96 and 97 respectively which arecontrolled by the microscope controller 31 (FIG. 3) and are notconsidered part of the slide handling subsystem. The X-Y stage 38further includes an aperture 55 for allowing illumination to reach theslide carrier. A switch 91 is mounted adjacent the aperture 55 forsensing contact with the carrier and thereupon activating a motor 87 todrive stage drive belt 50 (FIG. 7 b). The drive belt 50 is a doublesided timing belt having teeth for engaging pitch rack 68 of the carrier60 (FIG. 6 b).

The slide output module 17 includes slide carrier output hopper 18,unloading platform 36 and slide carrier unloading subassembly 34. Theunloading subassembly 34 comprises a motor 89 for rotating the unloadingplatform 36 about shaft 98 during an unloading operation describedfurther below. An outfeed gear 93 driven by motor 88 rotatably engagesthe pitch rack 68 of the carrier 60 (FIG. 6 b) to transport the carrierto a rest position against switch 92. A springloaded hold-down mechanismholds the carrier in place on the unloading platform 36.

The slide handling operation will now be described. Referring to FIG. 8,a series of slide carriers 60 are shown stacked in input hopper 16 withthe top edges 60 a aligned. As the slide handling operation begins, theindexing cam 56 driven by motor 85 advances one revolution to allow onlyone slide carrier to drop to the bottom of the hopper 16 and onto theloading platform 52.

FIGS. 8 a-8 d show the cam action in more detail. The cam 56 includes ahub 56 a to which are mounted upper and lower leaves 56 b and 56 crespectively. The leaves 56 b, 56 c are semicircular projectionsoppositely positioned and spaced apart vertically. In a first positionshown in FIG. 8 a, the upper leaf 56 b supports the bottom carrier atthe undercut portion 66. At a position of the cam 56 rotated 180°, shownin FIG. 8 b, the upper leaf 56 b no longer supports the carrier andinstead the carrier has dropped slightly and is supported by the lowerleaf 56 c. FIG. 8 c shows the position of the cam 56 rotated 270.degree.wherein the upper leaf 56 b has rotated sufficiently to begin to engagethe undercut 66 of the next slide carrier while the opposite facinglower leaf 56 c still supports the bottom carrier. After a full rotationof 360° as shown in FIG. 5 d, the lower leaf 56 c has rotated oppositethe carrier stack and no longer supports the bottom carrier which nowrests on the loading platform 52. At the same position, the upper leaf56 b supports the next carrier for repeating the cycle.

Referring again to FIGS. 7 a and 7 b, when the carrier drops to theloading platform 52, the contact closes switch 90 which activates motors86 and 87. Motor 86 drives the infeed drive belt 59 until the pusher tab58 makes contact with the carrier and pushes the carrier onto the X-Ystage drive belt 50. The stage drive belt 50 advances the carrier untilcontact is made with switch 91, the closing of which begins the slidescanning process described further herein. Upon completion of thescanning process, the X-Y stage 38 moves to an unload position andmotors 87 and 88 are activated to transport the carrier to the unloadingplatform 36 using stage drive belt 50. As noted, motor 88 drives outfeedgear 93 to engage the carrier pitch rack 68 of the carrier 60 (FIG. 6 b)until switch 92 is contacted. Closing switch 92 activates motor 89 torotate the unloading platform 36.

The unloading operation is shown in more detail in end views of theoutput module 17 (FIGS. 9 a-9 d). In FIG. 9 a, the unloading platform 36is shown in a horizontal position supporting a slide carrier 60. Thehold-down mechanism 94 secures the carrier 60 at one end. FIG. 9 b showsthe output module 17 after motor 89 has rotated the unloading platform36 to a vertical position, at which point the spring loaded hold-downmechanism 94 releases the slide carrier 60 into the output hopper 18.The carrier 60 is supported in the output hopper 18 by means of ears 64(FIGS. 6 a and 6 b). FIG. 9 e shows the unloading platform 36 beingrotated back towards the horizontal position. As the platform 36 rotatesupward, it contacts the deposited carrier 60 and the upward movementpushes the carrier toward the front of the output hopper 18. FIG. 9 dshows the unloading platform 36 at its original horizontal positionafter having output a series of slide carriers 60 to the output hopper18.

Having described the overall system and the automated slide handlingfeature, the aspects of the apparatus 10 relating to scanning, focusingand image processing will now be described in further detail.

In some cases, an operator will know ahead of time where the scan areaof interest is on the slide. Conventional preparation of slides forexamination provides repeatable and known placement of the sample on theslide. The operator can therefore instruct the system to always scan thesame area at the same location of every slide which is prepared in thisfashion. But there are other times in which the area of interest is notknown, for example, where slides are prepared manually with a knownsmear technique. One feature of the invention automatically determinesthe scan area using a texture analysis process.

FIG. 10 is a flow diagram that describes the processing associated withthe automatic location of a scan area. As shown in this figure, thebasic method is to pre-scan the entire slide area to determine texturefeatures that indicate the presence of a smear and to discriminate theseareas from dirt and other artifacts.

At each location of this raster scan, an image such as in FIG. 12 isacquired and analyzed for texture information at steps 204 and 206.Since it is desired to locate the edges of the smear sample within agiven image, texture analyses are conducted over areas called windows78, which are smaller than the entire image as shown in FIG. 12. Theprocess iterates the scan across the slide at steps 208, 210, 212 and214.

In the interest of speed, the texture analysis process is performed at alower magnification, preferably at a 4× objective. One reason to operateat low magnification is to image the largest slide area at any one time.Since cells do not yet need to be resolved at this stage of the overallimage analysis, the 4× magnification is preferred. On a typical slide,as shown in FIG. 11, a portion 72 b of the end of the slide 72 isreserved for labeling with identification information. Excepting thislabel area, the entire slide is scanned in a raster scan fashion 76 toyield a number of adjacent images.

Texture values for each window include the pixel variance over a window,the difference between the largest and smallest pixel value within awindow, and other indicators. The presence of a smear raises the texturevalues compared with a blank area.

One problem with a smear from the standpoint of determining its locationis its non-uniform thickness and texture. For example, the smear islikely to be relatively thin at the edges and thicker towards the middledue to the nature of the smearing process. To accommodate for thenon-uniformity, texture analysis provides a texture value for eachanalyzed area. The texture value tends to gradually rise as the scanproceeds across a smear from a thin area to a thick area, reaches apeak, and then falls off again to a lower value as a thin area at theedge is reached. The problem is then to decide from the series oftexture values the beginning and ending, or the edges, of the smear. Thetexture values are fit to a square wave waveform since the texture datadoes not have sharp beginnings and endings.

After conducting this scanning and texture evaluation operation, onemust determine which areas of elevated texture values represent thedesired smear 74, and which represent undesired artifacts. This isaccomplished by fitting a step function, on a line by line basis to thetexture values in step 216. This function, which resembles a singlesquare wave across the smear with a beginning at one edge, and end atthe other edge, and an amplitude provides the means for discrimination.The amplitude of the best-fit step function is utilized to determinewhether smear or dirt is present since relatively high values indicatesmear. If it is decided that smear is present, the beginning and endingcoordinates of this pattern are noted until all lines have beenprocessed, and the smear sample area defined at 218.

After an initial focusing operation described further herein, the scanarea of interest is scanned to acquire images for image analysis. Thepreferred method of operation is to initially perform a complete scan ofthe slide at low magnification to identify and locate candidate objectsof interest, followed by further image analysis of the candidate objectsof interest at high magnification in order to confirm the objects ascells. An alternate method of operation is to perform high magnificationimage analysis of each candidate object of interest immediately afterthe object has been identified at low magnification. The lowmagnification scanning then resumes, searching for additional candidateobjects of interest. Since it takes on the order of a few seconds tochange objectives, this alternate method of operation would take longerto complete.

The operator can pre-select a magnification level to be used for thescanning operation. A low magnification using a 10× objective ispreferred for the scanning operation since a larger area can beinitially analyzed for each acquired scan image. The overall detectionprocess for a cell includes a combination of decisions made at both low(10×) and high magnification (40×) levels. Decision making at the 10×magnification level is broader in scope, i.e., objects that loosely fitthe relevant color, size and shape characteristics are identified at the10× level. Analysis at the 40× magnification level then proceeds torefine the decision making and confirm objects as likely cells orcandidate objects of interest. For example, at the 40× level it is notuncommon to find that some objects that were identified at 10× areartifacts which the analysis process will then reject. In addition,closely packed objects of interest appearing at 10× are separated at the40× level.

In a situation where a cell straddles or overlaps adjacent image fields,image analysis of the individual adjacent image fields could result inthe cell being rejected or undetected. To avoid missing such cells, thescanning operation compensates by overlapping adjacent image fields inboth the x and y directions. An overlap amount greater than half thediameter of an average cell is preferred. In the preferred embodiment,the overlap is specified as a percentage of the image field in the x andy directions.

The time to complete an image analysis can vary depending upon the sizeof the scan area and the number of candidate cells, or objects ofinterest identified. For one example, in the preferred embodiment, acomplete image analysis of a scan area of two square centimeters inwhich 50 objects of interest are confirmed can be performed in about 12to 15 minutes. This example includes not only focusing, scanning andimage analysis but also the saving of 40× images as a mosaic on harddrive 21 (FIG. 2).

Consider the utility of the present invention in a “rare event”application where there may be one, two or a very small number of cellsof interest located somewhere on the slide. To illustrate the nature ofthe problem by analogy, if one were to scale a slide to the size of afootball field, a tumor cell, for example, would be about the size of abottle cap. The problem is then to rapidly search the football field andfind the very small number of bottle caps and have a high certainty thatnone have been missed.

However the scan area is defined, an initial focusing operation must beperformed on each slide prior to scanning. This is required since slidesdiffer, in general, in their placement in a carrier. These differencesinclude slight (but significant) variations of tilt of the slide in itscarrier. Since each slide must remain in focus during scanning, thedegree of tilt of each slide must be determined. This is accomplishedwith an initial focusing operation that determines the exact degree oftilt, so that focus can be maintained automatically during scanning.

The initial focusing operation and other focusing operations to bedescribed later utilize a focusing method based on processing of imagesacquired by the system. This method was chosen for its simplicity overother methods including use of IR beams reflected from the slide surfaceand use of mechanical gauges. These other methods also would notfunction properly when the specimen is protected with a coverglass. Thepreferred method results in lower system cost and improved reliabilitysince no additional parts need be included to perform focusing.

FIG. 13A provides a flow diagram describing the “focus point” procedure.The basic method relies on the fact that the pixel value variance (orstandard deviation) taken about the pixel value mean is maximum at bestfocus. A “brute-force” method could simply step through focus, using thecomputer controlled Z, or focus stage, calculate the pixel variance ateach step, and return to the focus position providing the maximumvariance. Such a method would be too time consuming. Therefore,additional features were added as shown in FIG. 13A.

These features include the determination of pixel variance at arelatively coarse number of focal positions, and then the fitting of acurve to the data to provide a faster means of determining optimalfocus. This basic process is applied in two steps, coarse and fine.

During the coarse step at 220-230, the Z stage is stepped over auser-specified range of focus positions, with step sizes that are alsouser-specified. It has been found that for coarse focusing, these dataare a close fit to a Gaussian function. Therefore, this initial set ofvariance versus focus position data are least-squares fit to a Gaussianfunction at 228. The location of the peak of this Gaussian curvedetermines the initial or coarse estimate of focus position for input tostep 232.

Following this, a second stepping operation 232-242 is performedutilizing smaller steps over a smaller focus range centered on thecoarse focus position. Experience indicates that data taken over thissmaller range are generally best fit by a second order polynomial. Oncethis least squares fit is performed at 240, the peak of the second ordercurve provides the fine focus position at 244.

FIG. 14 illustrates a procedure for how this focusing method is utilizedto determine the orientation of a slide in its carrier. As shown, focuspositions are determined, as described above, for a 3×3 grid of pointscentered on the scan area at 264. Should one or more of these points lieoutside the scan area, the method senses at 266 this by virtue of lowvalues of pixel variance. In this case, additional points are selectedcloser to the center of the scan area. FIG. 15 shows the initial arrayof points 80 and new point 82 selected closer to the center. Once thisarray of focus positions is determined at 268, a least squares plane isfit to this data at 270. Focus points lying too far above or below thisbest-fit plane are discarded at 272 (such as can occur from a dirtycover glass over the scan area), and the data is then refit. This planeat 274 then provides the desired Z position information for maintainingfocus during scanning.

After determination of the best-fit focus plane, the scan area isscanned in an X raster scan over the scan area as described earlier.During scanning, the X stage is positioned to the starting point of thescan area, the focus (Z) stage is positioned to the best fit focusplane, an image is acquired and processed as described later, and thisprocess is repeated for all points over the scan area. In this way,focus is maintained automatically without the need for time-consumingrefocusing at points during scanning.

Prior to confirmation of cell objects at a 40× or 60× level, arefocusing operation is conducted since the use of this highermagnification requires more precise focus than the best-fit planeprovides. FIG. 16 provides the flow diagram for this process. As may beseen, this process is similar to the fine focus method described earlierin that the object is to maximize the image pixel variance. This isaccomplished by stepping through a range of focus positions with the Zstage at 276, 278, calculating the image variance at each position at278, fitting a second order polynomial to these data at 282, andcalculating the peak of this curve to yield an estimate of the bestfocus position at 284, 286. This final focusing step differs fromprevious ones in that the focus range and focus step sizes are smallersince this magnification requires focus settings to within 0.5 micron orbetter.

It should be noted that for some combinations of cell stainingcharacteristics, improved focus can be obtained by numerically selectingthe focus position that provides the largest variance, as opposed toselecting the peak of the polynomial. In such cases, the polynomial isused to provide an estimate of best focus, and a final step selects theactual Z position giving highest pixel variance. It should also be notedthat if at any time during the focusing process at 40× or 60× theparameters indicate that the focus position is inadequate, the systemautomatically reverts to a coarse focusing process as described abovewith reference to FIG. 13A. This ensures that variations in specimenthickness can be accommodated in an expeditious manner.

For some biological specimens and stains, the focusing methods discussedabove do not provide optimal focused results. For example, certain whiteblood cells known as neutrophils may be stained with Fast Red, acommonly known stain, to identify alkaline phosphatase in the cytoplasmof the cells. To further identify these cells and the material withinthem, the specimen may be counterstained with hemotoxylin to identifythe nucleus of the cells. In cells so treated, the cytoplasm bearingalkaline phosphatase becomes a shade of red proportionate to the amountof alkaline phosphatase in the cytoplasm and the nucleus becomes blue.However, where the cytoplasm and nucleus overlap, the cell appearspurple. These color combinations appear to preclude the finding of afocused Z position using the focus processes discussed above.

In an effort to find a best focal position at high magnification, afocus method, such as the one shown in FIG. 13B may be used. That methodbegins by selecting a pixel near the center of a candidate object ofinterest (Block 248) and defining a region of interest centered aboutthe selected pixel (Block 250). Preferably, the width of the region ofinterest is a number of columns which is a power of 2. This widthpreference arises from subsequent processing of the region of interestpreferably using a one dimensional Fast Fourier Transform (FFT)technique. As is well known within, the art, processing columns of pixelvalues using the FFT technique is facilitated by making the number ofcolumns to be processed a power of two. While the height of the regionof interest is also a power of two in the preferred embodiment, it neednot be unless a two dimensional FFT technique is used to process theregion of interest.

After the region of interest is selected, the columns of pixel valuesare processed using the preferred one dimensional FFT to determine aspectra of frequency components for the region of interest (Block 252).The frequency spectra ranges from DC to some highest frequencycomponent. For each frequency component, a complex magnitude iscomputed. Preferably, the complex magnitudes for the frequencycomponents which range from approximately 25% of the highest componentto approximately 75% of the highest component are squared and summed todetermine the total power for the region of interest (Block 254).Alternatively, the region of interest may be processed with a smoothingwindow, such as a Hanning window, to reduce the spurious high frequencycomponents generated by the FFT processing of the pixel values in theregion of interest. Such preprocessing of the region of interest permitsall complex magnitude over the complete frequency range to be squaredand summed. After the power for a region has been computed and stored(Block 256), a new focal position is selected, focus adjusted (Blocks258, 260), and the process repeated. After each focal position has beenevaluated, the one having the greatest power factor is selected as theone best in focus (Block 262).

The following describes the image processing methods which are utilizedto decide whether a candidate object of interest such as a stained tumorcell is present in a given image, or field, during the scanning process.Candidate objects of interest which are detected during scanning arereimaged at higher (40× or 60×) magnification, the decision confirmed,and a region of interest for this cell saved for later review by thepathologist.

The image processing includes color space conversion, low passfiltering, background suppression, artifact suppression, morphologicalprocessing, and blob analysis. One or more of these steps can optionallybe eliminated. The operator is provided with an option to configure thesystem to perform any or all of these steps and, whether to performcertain steps more than once or several times in a row. It should alsobe noted that the sequence of steps may be varied and thereby optimizedfor specific reagents or reagent combinations; however, the sequencedescribed herein is preferred. It should be noted that the imageprocessing steps of low pass filtering, thresholding, morphologicalprocessing, and blob analysis are generally known image processingbuilding blocks.

An overview of the preferred process is shown in FIG. 17A. The preferredprocess for identifying and locating candidate objects of interest in astained biological specimen on a slide begins with an acquisition ofimages obtained by scanning the slide at low magnification (Block 288).Each image is then converted from a first color space to a second colorspace (Block 290) and the color converted image is low pass filtered(Block 292). The pixels of the low pass filtered image are then comparedto a threshold (Block 294) and, preferably, those pixels having a valueequal to or greater than the threshold are identified as candidateobject of interest pixels and those less than the threshold aredetermined to be artifact or background pixels. The candidate object ofinterest pixels are then morphologically processed to identify groups ofcandidate object of interest pixels as candidate objects of interest(Block 296). These candidate objects of interest are then compared toblob analysis parameters (Block 298) to further differentiate candidateobjects of interest from objects which do not conform to the blobanalysis parameters and, thus, do not warrant further processing. Thelocation of the candidate objects of interest may be stored prior toconfirmation at high magnification. The process continues by determiningwhether the candidate objects of interest have been confirmed (Block300). If they have not been confirmed, the optical system is set to highmagnification (Block 302) and images of the slide at the locationscorresponding to the candidate objects of interest identified in the lowmagnification images are acquired (Block 288). These images are thencolor converted (Block 290), low pass filtered (Block 292), compared toa threshold (Block 294), morphologically processed (Block 296), andcompared to blob analysis parameters (Block 298) to confirm whichcandidate objects of interest located from the low magnification imagesare objects of interest. The coordinates of the objects of interest arethen stored for future reference (Block 303).

Neural net processing schemes were not considered for the preferredembodiment for several reasons. Firstly, the preferred embodiment isoptimized for “rare-event” detection, although it is not limited to thiscase. Since neural nets must be trained on what to look for, sometimesseveral thousands of examples must be presented to the neural net forthis training. This is impractical for a rare-event application.Secondly, neural net processing can be slower than “deterministic”methods, sometimes by large factors. Therefore, neural nets were notdeemed appropriate for this application, although certain features ofthe invention may be advantageously applied to neural network systems.

In general, the candidate objects of interest, such as tumor cells, aredetected based on a combination of characteristics, including size,shape, and color. The chain of decision making based on thesecharacteristics preferably begins with a color space conversion process.The CCD camera coupled to the microscope subsystem outputs a color imagecomprising a matrix of 640×480 pixels. Each pixel comprises red, greenand blue (RGB) signal values.

It is desirable to transform the matrix of RGB values to a differentcolor space because the difference between candidate objects of interestand their background, such as tumor and normal cells, may be determinedfrom their respective colors. Specimens are generally stained with oneor more industry standard stains (e.g., DAB, New Fuchsin, AEC) which are“reddish” in color. Candidate objects of interest retain more of thestain and thus appear red while normal cells remain unstained. Thespecimens may also be counterstained with hematoxalin so the nuclei ofnormal cells or cells not containing an object of interest appear blue.In addition to these objects, dirt and debris can appear as black, gray,or can also be lightly stained red or blue depending on the stainingprocedures utilized. The residual plasma or other fluids also present ona smear may also possess some color.

In the color conversion operation, a ratio of two of the RGB signalvalues is formed to provide a means for discriminating colorinformation. With three signal values for each pixel, nine differentratios can be formed: R/R, R/G, R/B, G/G, G/B, G/R, B/B, B/G, B/R. Theoptimal ratio to select depends upon the range of color informationexpected in the slide specimen. As noted above, typical stains used fordetecting candidate objects of interest such as tumor cells arepredominantly red, as opposed to predominantly green or blue. Thus, thepixels of a cell of interest which has been stained contain a redcomponent which is larger than either the green or blue components. Aratio of red divided by blue A) provides a value which is greater thanone for tumor cells but is approximately one for any clear or whiteareas on the slide. Since the remaining cells, i.e., normal cells,typically are stained blue, the RIB ratio for pixels of these lattercells yields values of less than one. The RIB ratio is preferred forclearly separating the color information typical in these applications.

FIG. 17B illustrates the flow diagram by which this conversion isperformed. In the interest of processing speed, the conversion isimplemented with a look up table. The use of a look up table for colorconversion accomplishes three functions: 1) performing a divisionoperation; 2) scaling the result for processing as an image having pixelvalues ranging from 0 to 255; and 3) defining objects which have lowpixel values in each color band (R,G,B) as “black” to avoid infiniteratios (i.e., dividing by zero). These “black” objects are typicallystaining artifacts or can be edges of bubbles caused by pasting acoverglass over the specimen.

Once the look up table is built at 304 for the specific color ratio(i.e., choices of tumor and nucleated cell stains), each pixel in theoriginal RGB image is converted at 308 to produce the output. Since itis of interest to separate the red stained tumor cells from blue stainednormal ones, the ratio of color values is then scaled by a userspecified factor. As an example, for a factor of 128 and the ratio of(red pixel value)/(blue pixel value), clear areas on the slide wouldhave a ratio of 1 scaled by 128 for a final X value of 128. Pixels whichlie in red stained tumor cells would have X value greater than 128,while blue stained nuclei of normal cells would have value less than128. In this way, the desired objects of interest can be numericallydiscriminated. The resulting 640×480 pixel matrix, referred to as theX-image, is a gray scale image having values ranging from 0 to 255.

Other methods exist for discriminating color information. One classicalmethod converts the RGB color information into another color space, suchas HSI (hue, saturation, intensity) space. In such a space, distinctlydifferent hues such as red, blue, green, yellow, may be readilyseparated. In addition, relatively lightly stained objects may bedistinguished from more intensely stained ones by virtue of differingsaturations. However, converting from RGB space to HSI space requiresmore complex computation. Conversion to a color ratio is faster; forexample, a full image can be converted by the ratio technique of thepresent invention in about 30 ms while an HSI conversion can takeseveral seconds.

In yet another approach, one could obtain color information by taking asingle color channel from the camera. As an example, consider a bluechannel, in which objects that are red are relatively dark. Objectswhich are blue, or white, are relatively light in the blue channel. Inprinciple, one could take a single color channel, and simply set athreshold wherein everything darker than some threshold is categorizedas a candidate object of interest, for example, a tumor cell, because itis red and hence dark in the channel being reviewed. However, oneproblem with the single channel approach occurs where illumination isnot uniform. Non-uniformity of illumination results in non-uniformityacross the pixel values in any color channel, for example, tending topeak in the middle of the image and dropping off at the edges where theillumination falls off. Performing thresholding on this non-uniformcolor information runs into problems, as the edges sometimes fall belowthe threshold, and therefore it becomes more difficult to pick theappropriate threshold level. However, with the ratio technique, if thevalues of the red channel fall off from center to edge, then the valuesof the blue channel also fall off center to edge, resulting in a uniformratio. Thus, the ratio technique is more immune to illuminationnon-uniformities.

As previously described, the color conversion scheme is relativelyinsensitive to changes in color balance, i.e., the relative outputs ofthe red, green, and blue channels. However, some control is necessary toavoid camera saturation, or inadequate exposures in any one of the colorbands. This color balancing is performed automatically by utilizing acalibration slide consisting of a clear area, and a “dark” area having aknown optical transmission or density. The system obtains images fromthe clear and “dark” areas, calculates “white” and “black” adjustmentsfor the image processor 25, and thereby provides correct color balance.

In addition to the color balance control, certain mechanical alignmentsare automated in this process. The center point in the field of view forthe various microscope objectives as measured on the slide can vary byseveral (or several tens of) microns. This is the result of slightvariations in position of the microscope objectives 44 a as determinedby the turret 44 (FIG. 4), small variations in alignment of theobjectives with respect to the system optical axis, and other factors.Since it is desired that each microscope objective be centered at thesame point, these mechanical offsets must be measured and automaticallycompensated.

This is accomplished by imaging a test slide which contains arecognizable feature or mark. An image of this pattern is obtained bythe system with a given objective, and the position of the markdetermined. The system then rotates the turret to the next lensobjective, obtains an image of the test object, and its position isredetermined. Apparent changes in position of the test mark are recordedfor this objective. This process is continued for all objectives.

Once these spatial offsets have been determined, they are automaticallycompensated for by moving the stage 38 by an equal (but opposite) amountof offset during changes in objective. In this way, as different lensobjectives are selected, there is no apparent shift in center point orarea viewed.

A low pass filtering process precedes thresholding. An objective ofthresholding is to obtain a pixel image matrix having only candidateobjects of interest, such as tumor cells above a threshold level andeverything else below it. However, an actual acquired image will containnoise. The noise can take several forms, including white noise andartifacts. The microscope slide can have small fragments of debris thatpick up color in the staining process and these are known as artifacts.These artifacts are generally small and scattered areas, on the order ofa few pixels, which are above the threshold. The purpose of low passfiltering is to essentially blur or smear the entire color convertedimage. The low pass filtering process will smear artifacts more thanlarger objects of interest such as tumor cells and thereby eliminate orreduce the number of artifacts that pass the thresholding process. Theresult is a cleaner thresholded image downstream.

In the low pass filter process, a 3×3 matrix of coefficients is appliedto each pixel in the 640×480×-image. A preferred coefficient matrix isas follows:

$\mspace{20mu} {\quad\begin{bmatrix}{1/9} & {1/9} & {1/9} \\{1/9} & {1/9} & {1/9} \\{1/9} & {1/9} & {1/9}\end{bmatrix}}$

At each pixel location, a 3×3 matrix comprising the pixel of interestand its neighbors is multiplied by the coefficient matrix and summed toyield a single value for the pixel of interest. The output of thisspatial convolution process is again a 640×480 matrix.

As an example, consider a case where the center pixel and only thecenter pixel, has a value of 255 and each of its other neighbors, topleft, top, top right and so forth, have values of 0. This singular whitepixel case corresponds to a small object. The result of the matrixmultiplication and addition using the coefficient matrix is a value of1/9(255) or 28 for the center pixel, a value which is below the nominalthreshold of 128. Now consider another case in which all the pixels havea value of 255 corresponding to a large object. Performing the low passfiltering operation on a 3×3 matrix for this-case yields a value of 255for the center pixel. Thus, large objects retain their values whilesmall objects are reduced in amplitude or eliminated. In the preferredmethod of operation, the low pass filtering process is performed on theX image twice in succession.

In order to separate objects of interest, such as a tumor cell in the ximage from other objects and background, a thresholding operation isperformed designed to set pixels within cells of interest to a value of255, and all other areas to 0. Thresholding ideally yields an image inwhich cells of interest are white and the remainder of the image isblack. A problem one faces in thresholding is where to set the thresholdlevel. One cannot simply assume that cells of interest are indicated byany pixel value above the nominal threshold of 128. A typical imagingsystem may use an incandescent halogen light bulb as a light source. Asthe bulb ages, the relative amounts of red and blue output can change.The tendency as the bulb ages is for the blue to drop off more than thered and the green. To accommodate for this light source variation overtime, a dynamic thresholding process is used whereby the threshold isadjusted dynamically for each acquired image. Thus, for each 640×480image, a single threshold value is derived specific to that image.

As shown in FIG. 18, the basic method is to calculate, for each field,the mean X value, and the standard deviation about this mean at 312. Thethreshold is then set at 314 to the mean plus an amount defined by theproduct of a (user specified) factor and the standard deviation of thecolor converted pixel values. The standard deviation correlates to thestructure and number of objects in the image. Preferably, the userspecified factor is in the range of approximately 1.5 to 2.5. The factoris selected to be in the lower end of the range for slides in which thestain has primarily remained within cell boundaries and the factor isselected to be in the upper end of the range for slides in which thestain is pervasively present throughout the slide. In this way, as areasare encountered on the slide with greater or lower backgroundintensities, the threshold may be raised or lowered to help reducebackground objects. With this method, the threshold changes in step withthe aging of the light source such that the effects of the aging arecancelled out. The image matrix resulting at 316 from the thresholdingstep is a binary image of black (O) and white (255) pixels.

As is often the case with thresholding operations such as that describedabove, some undesired areas will lie above the threshold value due tonoise, small stained cell fragments, and other artifacts. It is desiredand possible to eliminate these artifacts by virtue of their small sizecompared with legitimate cells of interest. Morphological processes areutilized to perform this function.

Morphological processing is similar to the low pass filter convolutionprocess described earlier except that it is applied to a binary image.Similar to spatial convolution, the morphological process traverses aninput image matrix, pixel by pixel, and places the processed pixels inan output matrix. Rather than calculating a weighted sum of neighboringpixels as in the low pass convolution process, the morphological processuses set theory operations to combine neighboring pixels in a nonlinearfashion.

Erosion is a process whereby a single pixel layer is taken away from theedge of an object. Dilation is the opposite process which adds a singlepixel layer to the edges of an object. The power of morphologicalprocessing is that it provides for further discrimination to eliminatesmall objects that have survived the thresholding process and yet arenot likely tumor cells. The erosion and dilation processes that make upa morphological “open” preferably make small objects disappear yetallows large objects to remain. Morphological processing of binaryimages is described in detail in “Digital Image Processing”, pages127-137, G. A. Baxes, John Wiley & Sons, (1994).

FIG. 19 illustrates the flow diagram for this process. As shown here, amorphological “open” process performs this suppression. A singlemorphological open consists of a single morphological erosion 320followed by a single morphological dilation 322. Multiple “opens”consist of multiple erosions followed by multiple dilations. In thepreferred embodiment, one or two morphological opens are found to besuitable.

At this point in the processing chain, the processed image containsthresholded objects of interest, such as tumor cells (if any werepresent in the original image), and possibly some residual artifactsthat were too large to be eliminated by the processes above.

FIG. 20 provides a flow diagram illustrating a blob analysis performedto determine the number, size, and location of objects in thethresholded image. A blob is defined as a region of connected pixelshaving the same “color”, in this case, a value of 255. Processing isperformed over the entire image to determine the number of such regionsat 324 and to determine the area and x,y coordinates for each detectedblob at 326.

Comparison of the size of each blob to a known minimum area at 328 for atumor cell allows a refinement in decisions about which objects areobjects of interest, such as tumor cells, and which are artifacts. Thelocation (x,y coordinates) of objects identified as cells of interest inthis stage are saved for the final 40× reimaging step described below.Objects not passing the size test are disregarded as artifacts.

The processing chain described above identifies objects at the scanningmagnification as cells of interest candidates. As illustrated in FIG.21, at the completion of scanning, the system switches to the 40×magnification objective at 330, and each candidate is reimaged toconfirm the identification 332. Each 40× image is reprocessed at 334using the same steps as described above but with test parameterssuitably modified for the higher magnification (e.g. area). At 336, aregion of interest centered on each confirmed cell is saved to the harddrive for review by the pathologist.

As noted earlier, a mosaic of saved images is made available for viewingby the pathologist. As shown in FIG. 22, a series of images of cellswhich have been confirmed by the image analysis is presented in themosaic 150. The pathologist can then visually inspect the images to makea determination whether to accept (152) or reject (153) each cell image.Such a determination can be noted and saved with the mosaic of imagesfor generating a printed report.

In addition to saving the image of the cell and its region, the cellcoordinates are saved should the pathologist wish to directly view thecell through the oculars or on the image monitor. In this case, thepathologist reloads the slide carrier, selects the slide and cell forreview from a mosaic of cell images, and the system automaticallypositions the cell under the microscope for viewing.

It has been found that normal cells whose nuclei have been stained withhematoxylin are often quite numerous, numbering in the thousands per 10×image. Since these cells are so numerous, and since they tend to clump,counting each individual nucleated cell would add an excessiveprocessing burden, at the expense of speed, and would not necessarilyprovide an accurate count due to clumping. The apparatus performs anestimation process in which the total area of each field that is stainedhematoxylin blue is measured and this area is divided by the averagesize of a nucleated cell. FIG. 23 outlines this process.

In this process, a single color band (the red channel provides the bestcontrast for blue stained nucleated cells) is processed by calculatingthe average pixel value for each field at 342, establishing twothreshold values (high and low) as indicated at 344, 346, and countingthe number of pixels between these two values at 348. In the absence ofdirt, or other opaque debris, this provides a count of the number ofpredominantly blue pixels. By dividing this value by the average areafor a nucleated cell at 350, and looping over all fields at 352, anapproximate cell count is obtained. Preliminary testing of this processindicates an accuracy with +/−15%. It should be noted that for someslide preparation techniques, the size of nucleated cells can besignificantly larger than the typical size. The operator can select theappropriate nucleated cell size to compensate for these characteristics.

As with any imaging system, there is some loss of modulation transfer(i.e. contrast) due to the modulation transfer function (MTF)characteristics of the imaging, optics, camera, electronics, and othercomponents. Since it is desired to save “high quality” images of cellsof interest both for pathologist review and for archival purposes, it isdesired to compensate for these MTF losses.

An MTF compensation, or MTFC, is performed as a digital process appliedto the acquired digital images. A digital filter is utilized to restorethe high spatial frequency content of the images upon storage, whilemaintaining low noise levels. With this MTFC technology, image qualityis enhanced, or restored, through the use of digital processing methodsas opposed to conventional oil-immersion or other hardware basedmethods. MTFC is described further in “The Image Processing Handbook,”pages 225 and 337, J. C. Rues, CRC Press (1995).

Referring to FIG. 24, the functions available in a user interface of theapparatus 10 are shown. From the user interface, which is presentedgraphically on computer monitor 26, an operator can select amongapparatus functions which include acquisition 402, analysts 404, andsystem configuration 406. At the acquisition level 402, the operator canselect between manual 408 and automatic 410 modes of operation. In themanual mode, the operator is presented with manual operations 409.Patient information 414 regarding an assay can be entered at 412.

In the analysis level 404, review 416 and report 418 functions are madeavailable. At the review level 416, the operator can select a montagefunction 420. At this montage level, a pathologist can performdiagnostic review functions including visiting an image 422,accept/reject of cells 426, nucleated cell counting 426 accept/reject ofcell counts 428, and saving of pages at 430. The report level 418 allowsan operator to generate patient reports 432.

In the configuration level 406, the operator can select to configurepreferences at 434, input operator information 437 at 436, create asystem log at 438, and toggle a menu panel at 440. The configurationpreferences include scan area selection functions at 442, 452; montagespecifications at 444, bar code handling at 446, default cell countingat 448, stain selection at 450, and scan objective selection at 454.

EQUIVALENTS

While this invention has been particularly shown and described withreferences to preferred embodiments thereof, it will be understood bythose skilled in the art that various changes in form and details may bemade therein without departing from the spirit and scope of theinvention as defined by the appended claims.

1. An electronic microscope system, comprising: a processor; a movablestage, movable in two orthogonal directions, under control of theprocessor, said movable stage includes at least one part that determinesa current position of the movable stage; a microscope part, whichmagnifies a sample on the movable stage; an electronic camera part,which obtains an image of a magnified sample at a specified positioncontrolled by said movable stage; and at least one vibration isolationmount, coupled to said stage, and isolating vibration between saidmovable stage and said microscope part.
 2. A system as in claim 1,wherein said vibration isolation mount includes a high viscosity silicongel.
 3. A system as in claim 1, wherein said vibration isolation mountincludes a spring and piston.
 4. A system as in claim 1, wherein saidvibration isolation mount obtains damping factors on the order of 17 to20%.
 5. A system as in claim 1, wherein said movable stage is movable inx and y directions.
 6. A system as in claim 5, further comprising anx-position motor, moving the movable stage in an x direction, and a yposition motor, moving the stage in the y direction.
 7. A system as inclaim 5, wherein the processor controls storage of electronic imagesalong with information about x,y positions of the stage at the time whenthe electronic images were obtained.
 8. A method comprising: using aprocessor to move a sample holding stage; magnifying an image of an areaof the sample on the movable stage, where the area is based on a movedposition of the sample holding stage; obtaining an electronic fileindicative of the magnified image; and isolating vibration between saidmoving of said stage and said magnifying and obtaining.
 9. A method asin claim 8, wherein said isolating comprises using a high viscositysilicon gel to isolate said vibration.
 10. A method as in claim 8,wherein said isolating comprises using a spring and piston for isolatingthe vibration.
 11. A method as in claim 8, wherein said isolatingcomprises obtaining damping factors on the order of 17 to 20%.
 12. Amethod as in claim 8, wherein said using comprises moving the stage in Xand y directions.
 13. A method as in claim 12, wherein said movingcomprises controlling separate motors where an x-position motor iscontrolled to move the movable stage in an x direction, and a y positionmotor is controlled to move the stage in the y direction.
 14. A methodas in claim 12, further comprising storing information about x,ypositions of the stage at the time when the electronic files wereobtained.
 15. A method, comprising: obtaining an electronic version of amicroscope image; and determining information about colors within theimage by establishing a high threshold and a low threshold for aspecified color, counting a number of pixels that are in between saidhigh threshold and said low threshold, dividing the number of pixels bya value which relates pixels to cell size, and using a resultant numberas a count of the number of cells within the image.
 16. A method as inclaim 15, wherein said colors are colors of a stain on a slide.
 17. Amethod as in claim 16, wherein said stain is hematoxylin, and saidcolors are a blue color matching the characteristics of hematoxylin. 18.A method, comprising: staining a biological sample with a stain of aspecified color; obtaining an electronic version of a microscope imageof said biological sample; using said specified color to determine highthreshold and a low threshold around said specified color; analyzing theimage, to determine information about areas in the image that are inbetween said high threshold and said low threshold; and using saidinformation to determine a count of the number of stained cells in theimage.
 19. A method as in claim 18, wherein said using comprises,determining a number of pixels which are between said thresholds,dividing the number of pixels by a value which relates pixels to cellsize, and using a resultant number as a count of the number of cellswithin the image.